Siemens Corporation

Oxford Magnet Technology Limited

Siemens Aktiengesellschaft

Siemens Medical Solutions Usa, Inc.

Siemens Magnet Technology Ltd.

Marcel Jan Marie Kruip

Paul Beasley

Markus Vester

Oliver Heid

Francisco Miguel Hernandez-Guerra

Christopher Jude Amies

Juan Carlos Celi

Nicholas David Parker

Robert Andrew Slade

Peter Van Hasselt

Marijn Pieter Oomen

Hugh Alexander Blakes

Russell Peter Gore

Peter Jonathan Davis

Andrew Farquhar Atkins

Abdulbasad Shaikh

Mark Blumenthal

The invention relates to a combined radiation therapy and magnetic resonance unit. For this purpose, in accordance with the invention a combined radiation therapy and magnetic resonance unit is provided comprising a magnetic resonance diagnosis part with an interior, which is limited in radial direction by a main magnet, and a radiation therapy part for the irradiation of an irradiation area within the interior, wherein at least parts of the radiation therapy part, which comprise a beam deflection arrangement, are arranged within the interior.

Combined radiation therapy and magnetic resonance unit

Particle radiation therapy equipment arranged to apply a charged particle beam to a region of application in a predetermined direction, comprising a charged particle beam source arranged to direct a charged particle beam in the predetermined direction, further comprising magnetic field generation means for generating a magnetic field in an imaging volume which includes the region of application at the same time that the charged particle beam is applied, wherein the magnetic field generation means is arranged to provide access to the region of application for the charged particle beam, and to provide a homogeneous magnetic field in the region of application of the charged particle beam, said magnetic field being directed substantially in the predetermined direction.

Particle radiation therapy equipment

In a superconducting electromagnet system or method, cryogenically cooled magnet coils are arranged to provide a static magnetic field in an imaging region. A gradient coil assembly is arranged to provide oscillating magnetic fields within the imaging region. An electrically conductive shield is positioned between the cryogenically cooled magnet coils and the gradient coil assembly. The cryogenically cooled magnet coils are located within an outer vacuum chamber, and the electrically conductive shield is positioned outside the outer vacuum chamber between a surface of the outer vacuum chamber and the gradient coil assembly and inside a bore tube of the outer vacuum chamber. The conductive shield is supported on resilient damping mounts between the conductive shield and the gradient coil assembly and between the conductive shield and the bore tube of the outer vacuum chamber.

Electrically conductive shield for superconducting electromagnet system

A method for progressively introducing current into, or removing current from, a superconducting coil mounted on a former, in which the coil vibrates relative to the former.

Method for progressively introducing current into a superconducting coil mounted on a former

A bore tube for use in an imaging apparatus has a first tube and a second tube. The first tube is a complete cylinder of electrically conductive material; and the second tube is segmented into separate elements, each separately attached to the first tube.

Mass damped bore tube for imaging apparatus

A pulsed magnetic field is generated by a device having a magnet to be operated in pulse operation which contains at least one superconductive refrigerant-free winding that is disk-shaped or saddle-shaped. Also included is a refrigerating unit which has at least one cold head. A line system, having a refrigerant circulating in it according to a thermosiphon effect, thermally couples the winding to the cold head. The line system has a plurality of separate pipes lying next to one another. The pipes, open onto a common refrigerant distributor and closed at the other end, are thermally coupled to the surface of the disk-shaped or saddle-shaped winding.

Device for generating a pulsed magnetic field

A magnetic resonance device has a cryostat and a gradient coil assembly situated within an inner bore of the cryostat. A seal is positioned between the gradient coil assembly and the inner bore. The seal includes a first fluid filled toroid or helix mounted concentrically with the gradient coils; and a second fluid filled toroid or helix situated within the first toroid, or first helix.

Magnetic resonance device

Particle radiation therapy equipment arranged to apply a charged particle beam in a predetermined direction to a region of application within an imaging volume, comprising a charged particle beam source arranged to direct a charged particle beam in the predetermined direction, further comprising magnetic field generation means for generating a magnetic field in the region of application at the same time that the charged particle beam is applied, wherein the magnetic field generation means is arranged to provide access to the region of application for the charged particle beam, and to provide a homogeneous magnetic field in the region of application of the charged particle beam, said magnetic field being directed substantially in the predetermined direction.

An arrangement for producing an imaging region of increased maximum radial diameter in a magnetic resonance imaging (MRI) system, comprising a solenoidal magnet arrangement () comprising primary magnet coils () arranged symmetrically about an axis (A-A) and a shim coil set.

Shim for imaging magnets

A quench protection circuit for a superconducting magnet, comprises at least one heater associated with a corresponding coil of the superconducting magnet. The at least one heater is arranged to be driven by an inductor which is connected in series with it and is arranged to derive a voltage from variation in a magnetic field of the superconducting magnet. The at least one heater and the inductor are arranged in a series circuit which further comprises a non-linear positive temperature coefficient resistors.

Quench protection circuit for a superconducting magnet

The present invention provides a magnet assembly () comprising a pair of drive coils () symmetrically disposed with respect to a reference plane. The reference plane is located approximately equidistant between the drive coils. Each of the drive coils has a current flowing through it which is in the opposite sense to the current flowing through the other drive coil, such that a primary magnetic field is generated in a plane which is parallel to and substantially coincident with the reference plane. The assembly may comprise further compensating coils () which are configured to generate a magnetic field to improve homogeneity of the primary magnetic field. The drive coils and the compensating coils are generally in the shape of a racetrack and are preferably superconducting coils.

Open MRI magnet assembly with paired planar driving coils having opposite current flows and a racetrack, nested, or substantially-planar multi-coil shape

The present invention is a saturated ferromagnetic structure for controlling the homogeneity of the primary magnet field of a magnet in a Magnetic Resonance Imaging system. The structure has a plurality of coaxial laminations disposed thereon about a central axis of the structure, such that the structure is magnetically saturated and generates a magnetic field parallel to the central axis. In use the structure functions to improve the homogeneity of the primary magnetic field. The structure further allows for a MRI system with a less confined patient space than is currently available with known MRI systems.

Magnet assembly of an MRI system with concentric annular ferromagnetic laminations

The present invention relates to magnets and to magnetic resonance imaging systems. The magnet is open with magnetic coils arranged in quadrant, separated about two perpendicular planes, a midplane and a plane of reflection, and wherein the windings are configured such that, in operation, current flow is symmetrical about the plane of reflection and anti-symmetrical about the midplane, to produce a nett magnetic field at the center in a direction perpendicular to the plane of reflection.

Superconducting open MRI magnet with transverse magnetic field

The present invention is an improved magnet coil former for use in a magnetic resonance imaging (MRI) system. The improved magnetic coil former reduces the strength of the magnetic fields generated proximate the coils. This enables the coils to be driven at higher currents. The former consists of a substantially magnetically saturated ferromagnetic material and is arranged such that the compensating coil is magnetically attracted towards the former in a direction radially outward from the axis of the coils thereby reducing the collapsing hoop stress on the compensating coil. The former is made of Iron or other suitable ferromagnetic material. The former facilitates construction of a more compact MRI system.

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Oxford, United Kingdom

Marcel Jan Marie Kruip